Spectroscopic analyser

ABSTRACT

An analyser 10 for identifying or verifying or otherwise characterising a liquid based drug sample 16 comprising: an electromagnetic radiation source 11 for emitting electromagnetic radiation 14a in at least one beam at a sample 16, the electromagnetic radiation comprising at least two different wavelengths, a sample detector 17 that detects affected electromagnetic radiation resulting from the emitted electromagnetic radiation affected by the sample, and a processor 18 for identifying or verifying the sample from the detected affected electromagnetic radiation, wherein each wavelength or at least two of the wavelengths is between substantially 1300 nm and 2000 nm, and each wavelength or at least two of the wavelengths is in the vicinity of the wavelength(s) of (or within a region spanning) a spectral characteristic in the liquid spectrum between substantially 1300 nm and 2000 nm.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.14/110,134, filed May 19, 2014, which is a U.S. National Phase under 35U.S.C. § 371 of Intl Appl. No. PCT/NZ2012/000052, filed Apr. 10, 2012,designating the United States and published in English on Oct. 11, 2012as WO 2012/138236, which claims the benefit of priority to U.S.Provisional Appl. No. 61/472,290 filed Apr. 6, 2011. Any and allapplications for which a foreign or domestic priority claim isidentified in the Application Data Sheet as filed with the presentapplication are hereby incorporated by reference under 37 C.F.R. § 1.57.

BACKGROUND

Field

The present invention relates to a spectroscopic analyser, such as aspectrophotometer, for verifying and/or identifying or otherwiseanalysing drugs, blood or other substances.

Description of the Related Art

Spectroscopy, for example through the use of a spectroscopic analysersuch as a spectrophotometer, can be used to analyse substances. Forexample, by directing incident radiation towards a sample, and analysingthe spectral nature of the affected radiation, it can be possible togain an indication of the nature of the sample.

However, such analysers often provide inaccurate analysis. Accuratelydiscriminating between different substances can be difficult.

SUMMARY

It is an object of the present invention to provide an analyser and/ormethod for verifying or identifying or otherwise characterising a drugor other substances using spectroscopy.

In one aspect the present invention may be said to consist in ananalyser for identifying or verifying a liquid based drug samplecomprising: an electromagnetic radiation source for emittingelectromagnetic radiation in at least one beam at a sample, theelectromagnetic radiation comprising at least two different wavelengths,a sample detector that detects affected electromagnetic radiationresulting from the emitted electromagnetic radiation affected by thesample and provides output representing the detected affected radiation,and a processor for identifying or verifying the sample from thedetector output representing the detected affected electromagneticradiation, wherein each wavelength or at least two of the wavelengths isbetween substantially 1300 nm and 2000 nm, and each wavelength or atleast two of the wavelengths is in the vicinity of the wavelength(s) of(or within a region spanning) a spectral characteristic in the liquidspectrum between substantially 1300 nm and 2000 nm.

Preferably the electromagnetic radiation comprises a plurality ofelectromagnetic radiation beams, each beam having a differentwavelength.

Described herein is verifying or identifying the drug sample is againstcomparison data for one of a set of n drugs, and wherein theelectromagnetic radiation comprises at least log₂ n differentwavelengths in one or more beams.

Preferably the different wavelengths span or capture a plurality of atleast some of the spectral characteristics in the liquid spectrumbetween 1300 nm and 2000 nm.

Preferably the liquid spectrum comprises two or more spectralcharacteristics, and wherein: each spectral characteristic falls in orspans a region of the liquid spectrum, each wavelength falls within oneof the regions.

Described herein is each region is defined by a wavelength range.

Preferably the spectral characteristics comprise peaks, troughs,inflections, stable points or regions plateaus, knees and/or slopes ofthe liquid spectrum.

Preferably the liquid is water and comprises spectral characteristicsfalling in the following regions of the water spectrum: a first regionbetween 1300 nm and 1400 nm, a second region between 1400 nm and 1500nm, a third region between 1500 nm and 1600 nm, a fourth region between1600 nm and 1700 nm, a fifth region between 1700 nm and 1800 nm, and asixth region between 1800 nm and 200 nm.

Described herein is the electromagnetic radiation has an anchorwavelength in the vicinity of the wavelength(s) of (or within a regionspanning) a stable region in the liquid spectrum.

Described herein is each wavelength further corresponds to a wavelengthproduced by a source that is readily/cheaply obtainable.

Described herein is the source is a plurality of lasers, each laserconfigured to emit an electromagnetic radiation beam at a fixed ortuneable wavelength.

Preferably comprises a modulator for modulating the electromagneticradiation beam(s) emitted at the sample resulting in detected affectedradiation detected by the sample detector that is modulated wherein theprocessor as part of identifying or verifying the sample from the outputfrom the detector removes the dark current component from the outputrepresenting the detected affected modulated electromagnetic radiation

Optionally the processor removes the dark current component bymultiplying the output representing the detected affected modulatedelectromagnetic radiation by sine and cosine functions and integratingover the period of modulation oscillation to remove the dark currentcomponent.

Optionally the processor removes the dark current component byconducting a Fourier Transform on the output representing the modulateddetected affected radiation and removing the dark current component fromthe transformed.

Described herein is the processor identifies or verifies the drug sampleusing reference information.

Described herein is the affected electromagnetic radiation at or theelectromagnetic radiation beam comprising the anchor wavelength providesthe reference information.

Described herein is the analyser further comprises: an optical devicefor directing the plurality of electromagnetic radiation beams to areference sample, a reference detector that detects affectedelectromagnetic radiation beams affected by the reference sample toobtain the reference information and that passes the referenceinformation to the processor.

Described herein is the detector and/or source are temperaturecompensated to provide temperature stability, preferably usingthermistors and peltier devices in a closed loop system.

Described herein is each electromagnetic radiation beam is a highintensity narrowband light beam.

Described herein is the detector is a broadband photodiode that isbiased to have a response corresponding to the wavelengths of theaffected radiation.

Described herein is the emitted electromagnetic radiation beams from theplurality of lasers are directed to a sample path by one or more of: acarousel or carriage device to position the laser beams in the samplepath, or a prism, diffraction grating, beam splitter or other opticaldevice to redirect a radiation beam along the sample path.

Described herein is the processor receives: output representing theaffected electromagnetic radiation from the drug sample which providesdrug sample information, and optionally reference information for eachwavelength, and the processor: determines a representative value of thedrug sample information using that information and optionally referenceinformation for each wavelength.

Described herein is the sample information and reference informationcorrelate intensity and wavelength for each electromagnetic radiationbeam.

Described herein is the representative value corresponds to a best fitbetween the sample information and optionally the reference information.

Described herein is the representative value for the electromagneticradiation beam for each wavelength is compared to stored values toverify or identify the drug sample.

Described herein is the liquid is water, there are six electromagneticradiation beams and the wavelengths are substantially 1350 nm, 1450 nm,1550, nm, 1650, nm, 1750 nm and 1850 nm, and optionally wherein 1450 nmis the anchor wavelength.

Described herein is the sample is in an intravenous delivery device suchas an IV infusions set or syringe, or other receptacle such as atest-cell, test-tube, flow cell or the like.

Preferably the source is a laser comprising a photodetector, wherein thephotodetector detects electromagnetic radiation from the laser andoutputs the reference information.

In another aspect the present invention may be said to consist in amethod for identifying or verifying or otherwise characterising a liquidbased drug sample comprising: emitting electromagnetic radiation in atleast one beam at a sample, the electromagnetic radiation comprising atleast two different wavelengths, detecting affected electromagneticradiation resulting from the emitted electromagnetic radiation affectedby the sample and providing output representing the detected affectedradiation, and identifying or verifying the sample from the outputrepresenting detected affected electromagnetic radiation, wherein eachwavelength or at least two of the wavelengths is between substantially1300 nm and 2000 nm, and each wavelength or at least two of thewavelengths is in the vicinity of the wavelength(s) of (or within aregion spanning) a spectral characteristic in the liquid spectrumbetween substantially 1300 nm and 2000 nm.

Preferably the electromagnetic radiation comprises a plurality ofelectromagnetic radiation beams, each beam having a differentwavelength.

Described herein is verifying or identifying the drug sample is againstcomparison data for one of a set of n drugs, and wherein theelectromagnetic radiation comprises at least log₂ n differentwavelengths in one or more beams.

Preferably the different wavelengths span or capture a plurality of atleast some of the spectral characteristics in the liquid spectrumbetween 1300 nm and 2000 nm.

Preferably the liquid spectrum comprises two or more spectralcharacteristics, and wherein: each spectral characteristic falls in orspans a region of the liquid spectrum, each wavelength falls within oneof the regions.

Described herein is each region is defined by a wavelength range.

Preferably the spectral characteristics comprise peaks, troughs,inflections, stable points or regions, plateaus, knees and/or slopes ofthe liquid spectrum.

Preferably the liquid is water and comprises spectral characteristicsfalling in the following regions of the water spectrum: a first regionbetween 1300 nm and 1400 nm, a second region between 1400 nm and 1500nm, a third region between 1500 nm and 1600 nm, a fourth region between1600 nm and 1700 nm, a fifth region between 1700 nm and 1800 nm, and asixth region between 1800 nm and 200 nm.

Described herein is the electromagnetic radiation has an anchorwavelength in the vicinity of the wavelength(s) of (or within a regionspanning) a stable region in the liquid spectrum.

Described herein is each wavelength further corresponds to a wavelengthproduced by a source that is readily/cheaply obtainable.

Described herein is the electromagnetic radiation is generated using asource comprising a plurality of lasers, each laser configured to emitan electromagnetic radiation beam at a fixed or tuneable wavelength.

Described herein is wherein a modulator is used for modulating theelectromagnetic radiation beams emitted at the sample resulting indetected affected radiation that is modulated, and wherein identifyingor verifying the sample from the output from the output comprisesremoving the dark current component from the output representing thedetected affected modulated electromagnetic radiation.

Described herein is removing the dark current component comprisesmultiplying the output representing the detected affected modulatedelectromagnetic radiation by sine and cosine functions and integratingover the period of modulation oscillation to remove the dark currentcomponent.

Described herein is removing the dark current component comprisesconducting a Fourier Transform on the output representing the modulateddetected affected radiation and removing the dark current component fromthe transformed.

Described herein is the identifying or verifying is carried out by aprocessor that identifies or verifies the drug sample using referenceinformation.

Described herein is the affected electromagnetic radiation at or theelectromagnetic radiation beam comprising the anchor wavelength providesthe reference information.

Described herein is the method further comprises: directing theplurality of electromagnetic radiation beams to a reference sample usingan optical device, detecting using a reference detector affectedelectromagnetic radiation beams affected by the reference sample toobtain the reference information and that passes the referenceinformation to the processor.

Described herein is the method further comprises temperaturecompensating the detector and/or source provide temperature stability,preferably using thermistors and peltier devices in a closed loopsystem.

Described herein is each electromagnetic radiation beam is a highintensity narrowband light beam.

Described herein is the detector is a broadband photodiode that isbiased to have a response corresponding to the wavelength/s of theaffected radiation.

Described herein is the emitted electromagnetic radiation beams from theplurality of lasers are directed to a sample path by one or more of: acarousel or carriage device to position the laser beams in the samplepath, or a prism, diffraction grating, beam splitter or other opticaldevice to redirect a radiation beam along the sample path.

Described herein is the processor receives: affected electromagneticradiation from the drug sample which provides drug sample information,and optionally reference information for each wavelength, and theprocessor: determines a representative value of the drug sampleinformation and optionally reference information for each wavelength.

Described herein is the sample information and reference informationcorrelate intensity and wavelength for each electromagnetic radiationbeam.

Described herein is the representative value corresponds to a best fitbetween the sample information and optionally the reference information.

Described herein is the representative value for the electromagneticradiation beam for each wavelength is compared to stored values toverify or identify the drug sample.

Described herein is the liquid is water, there are six electromagneticradiation beams and the wavelengths are substantially 1350 nm, 1450 nm,1550, nm, 1650, nm, 1750 nm and 1850 nm, wherein 1450 nm is the anchorwavelength.

Described herein is the sample is in an intravenous delivery device suchas an IV infusions set or syringe, or other receptacle such as atest-cell, test-tube, flow cell or the like.

Preferably each laser comprises a photodetector, wherein thephotodetector detects electromagnetic radiation from the laser andoutputs the reference information.

In another aspect the present invention may be said to consist in ananalyser for identifying or verifying or otherwise characterising a drugsample (or other substance) in a liquid carrier comprising: anelectromagnetic radiation source for emitting electromagnetic radiationin at least one beam at a sample, the electromagnetic radiationcomprising at least two different selected wavelengths, a sampledetector that detects affected electromagnetic radiation resulting fromthe emitted electromagnetic radiation affected by the sample, and aprocessor for identifying or verifying the sample from the detectedaffected electromagnetic radiation, wherein each wavelength is selectedto be in the vicinity of the wavelength(s) of (or within a regionspanning) a spectral characteristic in the spectrum of the liquidcarrier, each wavelength falling within an analysis range suitable forthe liquid carrier.

In another aspect the present invention may be said to consist in amethod for identifying or verifying or otherwise characterising a drugsample (or other substance) in a liquid carrier comprising: emittingelectromagnetic radiation in at least one beam at a sample, theelectromagnetic radiation comprising at least two different selectedwavelengths, detecting affected electromagnetic radiation resulting fromthe emitted electromagnetic radiation affected by the sample, andidentifying or verifying the sample from the detected affectedelectromagnetic radiation, wherein each wavelength is selected to be inthe vicinity of the wavelength(s) of (or within a region spanning) aspectral characteristic in the spectrum of the liquid carrier, eachwavelength falling within an analysis range suitable for the liquidcarrier.

Described herein is an analyser, for identifying or verifying orotherwise characterising a liquid based drug sample (or other substance)comprising: an electromagnetic radiation source for emittingelectromagnetic radiation in at least one beam at a sample, theelectromagnetic radiation comprising at least two different wavelengths,a sample detector that detects affected electromagnetic radiationresulting from the emitted electromagnetic radiation affected by thesample, and a processor for identifying or verifying the sample from thedetected affected electromagnetic radiation, wherein each wavelength isfalls in an analysis range that provides improvedidentification/verification for drugs in the liquid carrier, and eachwavelength is in the vicinity of the wavelength(s) of (or within aregion spanning) a spectral characteristic in the liquid spectrum in theanalysis range.

Described herein is a method for identifying or verifying or otherwisecharacterising a liquid based drug sample (or other substance)comprising: emitting electromagnetic radiation in at least one beam at asample, the electromagnetic radiation comprising at least two differentwavelengths, detecting affected electromagnetic radiation resulting fromthe emitted electromagnetic radiation affected by the sample, andidentifying or verifying the sample from the detected affectedelectromagnetic radiation, wherein each wavelength is falls in ananalysis range that provides improved identification/verification fordrugs in the liquid carrier, and each wavelength is in the vicinity ofthe wavelength(s) of (or within a region spanning) a spectralcharacteristic in the liquid spectrum in the analysis range.

In another aspect the present invention an analyser for identifying orverifying or otherwise characterising a liquid based drug samplecomprising: an electromagnetic radiation source for emitting modulatedelectromagnetic radiation in at least one beam at a sample, theelectromagnetic radiation comprising at least two different wavelengths,a sample detector that detects affected modulated electromagneticradiation resulting from the emitted electromagnetic radiation affectedby the sample and provides output representing the detected affectedmodulated radiation, and a processor for identifying or verifying thesample from the output representing detected affected modulatedelectromagnetic radiation including removing dark current from theoutput, wherein each wavelength or at least two of the wavelengths isbetween substantially 1300 nm and 2000 nm.

In another aspect the present invention a method for identifying orverifying or otherwise characterising a liquid based drug samplecomprising: emitting modulated electromagnetic radiation in at least onebeam at a sample, the electromagnetic radiation comprising at least twodifferent wavelengths, detecting affected modulated electromagneticradiation resulting from the emitted electromagnetic radiation affectedby the sample and providing output representing the detected affectedradiation, and identifying or verifying the sample from the outputrepresenting detected affected modulated electromagnetic radiationincluding removing dart current from the output, wherein each wavelengthor at least two of the wavelengths is between substantially 1300 nm and2000 nm.

Described herein is an analyser for identifying or verifying orotherwise characterising a liquid based drug sample comprising: anelectromagnetic radiation source for emitting electromagnetic radiationin at least one beam at a sample, the electromagnetic radiationcomprising at least two different wavelengths and for measuring thepower of the emitted electromagnetic radiation, a sample detector thatdetects affected electromagnetic radiation resulting from the emittedelectromagnetic radiation affected by the sample and provides outputrepresenting the detected affected radiation, and a processor foridentifying or verifying the sample from the detector outputrepresenting the detected affected electromagnetic radiation includingusing the measured power of the emitted electromagnetic radiation,wherein each wavelength or at least two of the wavelengths is betweensubstantially 1300 nm and 2000 nm, and each wavelength or at least twoof the wavelengths is in the vicinity of the wavelength(s) of (or withina region spanning) a spectral characteristic in the liquid spectrumbetween substantially 1300 nm and 2000 nm.

Described herein is a method for identifying or verifying or otherwisecharacterising a liquid based drug sample comprising: emittingelectromagnetic radiation in at least one beam at a sample, theelectromagnetic radiation comprising at least two different wavelengthsand measuring the power of the emitted electromagnetic radiation,detecting affected electromagnetic radiation resulting from the emittedelectromagnetic radiation affected by the sample and providing outputrepresenting the detected affected radiation, and identifying orverifying the sample from the output representing detected affectedelectromagnetic radiation including using the measured power of theemitted electromagnetic radiation, wherein each wavelength or at leasttwo of the wavelengths is between substantially 1300 nm and 2000 nm.

Described herein is a analyser for identifying or verifying or otherwisecharacterising a sample comprising: an electromagnetic radiation sourcefor emitting electromagnetic radiation in at least one beam at a sample,the electromagnetic radiation comprising at least two differentwavelengths, a sample detector that detects affected electromagneticradiation resulting from the emitted electromagnetic radiation affectedby the sample, and a processor for identifying or verifying the samplefrom the detected affected electromagnetic radiation, wherein eachwavelength or at least two of the wavelengths is between substantially1300 nm and 2000 nm.

Preferably the source is a plurality of lasers in a single package, eachlaser configured to emit an electromagnetic radiation beam at a fixed ortuneable wavelength.

It is intended that reference to a range of numbers disclosed herein(for example, 1 to 10) also incorporates reference to all rationalnumbers within that range (for example, 1, 1.1, 2, 3, 3.9, 4, 5, 6, 6.5,7, 8, 9 and 10) and also any range of rational numbers within that range(for example, 2 to 8, 1.5 to 5.5 and 3.1 to 4.7). The term “comprising”as used in this specification means “consisting at least in part of”.Related terms such as “comprise” and “comprised” are to be interpretedin the same manner.

This invention may also be said broadly to consist in the parts,elements and features referred to or indicated in the specification ofthe application, individually or collectively, and any or allcombinations of any two or more of said parts, elements or features, andwhere specific integers are mentioned herein which have knownequivalents in the art to which this invention relates, such knownequivalents are deemed to be incorporated herein as if individually setforth.

BRIEF DESCRIPTION OF THE DRAWINGS

Preferred embodiments of the invention will be described with referenceto the following drawings, of which:

FIG. 1 shows in schematic form a spectroscopic analyser according to thepresent invention,

FIG. 2 shows in schematic form the hypothetical spectrum of ahypothetical liquid base/carrier,

FIG. 3 is a graph showing the error vs. number of wavelengths used inthe spectroscopic analyser,

FIG. 4 is a flow diagram showing operation of the spectroscopicanalyser,

FIG. 5 shows the spectrum of a drug (gelofusine succinated gelatinesolution 4%) overlaid the spectrum of a liquid based, being water,

FIG. 6 shows spectral characteristics of water between 1300 and 2000 nm,

FIG. 7 shows a schematic diagram of a first embodiment of thespectroscopic analyser in which the sources are lasers on a rotatingcarousel,

FIG. 8 shows a method of processing the output from the detectors,including a pre-processing and a verification/identification stage,

FIG. 9 shows a method of processing the output from the detectors,including a pre-processing and comparison data generation stage,

FIG. 10 shows a best fit line through data points obtained from outputsfrom the sample and reference detectors,

FIG. 11 shows a separation line between pre-processed data points for atraining sample and a comparison sample,

FIG. 12 shows a second embodiment in which the source comprises sixlasers that are directed along the sample path 14 a using a diffractiongrating,

FIG. 13 shows a third embodiment comprising a source of six lasers theoutputs of which are directed along a sample path using beam splitters,

FIG. 14 shows in schematic form a fourth embodiment for the sourcecomprising six lasers the outputs of which are converged onto a samplepath using a prism,

FIG. 15 shows a matrix indicating verification for a set of sampledrugs,

FIG. 16 shows an analyser using source modulation to eliminate areference channel,

FIG. 17 shows laser output power where the source is modulated,

FIG. 18 shows a schematic with a modulator,

FIG. 19 shows a flow diagram for extracting dark current

FIG. 20 shows in schematic form a fifth embodiment for the sourcecomprising six lasers the outputs of which are converged onto a samplepath using a planar lightwave circuit,

FIG. 21 shows in schematic form a sixth embodiment for the sourcecomprising a single package source and collimated lens.

DETAILED DESCRIPTION

Overview

FIG. 1 shows an overview of a spectroscopic analyser 10 (for example, aspectrophotometer) according to the present invention for verifying oridentifying (that is, analyse/characterise) drugs or other samples (e.g.blood, biological samples etc.). The term “drug” should be interpretedbroadly to cover any pharmaceutical or other medicament or substance fortreating patients, which is clinician controlled 9 (e.g. through ahospital, prescription or pharmacy) or freely available. The analyser(apparatus) 10 comprises a controller 12 that controls both physicalcontrol and processing aspects of operation. The analyser 10 comprisesan electromagnetic radiation source 11 for generating and emittingelectromagnetic radiation 22 with/at a plurality of wavelengths within awavelength range. The source might also have a photodetector 4 orsimilar for control purposes. The electromagnetic radiation could takethe form of a plurality of electromagnetic radiation beams at differentwavelengths, or a single electromagnetic radiation beam comprising aplurality of wavelength components.

The term “wavelength” used for electromagnetic radiation output refersto a particular wavelength, such as 1300 nm. As will be appreciated, inpractice, a source will not provide electromagnetic radiation outputwith a pure single wavelength—the output could contain components eitherside of the centre wavelength/peak. In this case, the term “wavelength”refers to the centre wavelength/peak of the electromagnetic radiationoutput, where the radiation output might also have a wavelengthcomponents either side of the centre wavelength, e.g. +/−30 nm, or +/−12nm or even just a few nm (e.g. 2 nm for lasers) either side. Each suchwavelength could be termed a “discrete” wavelength, as for practicalpurposes it is discrete, even if other components exist.

The electromagnetic radiation beams 22 could be visible light beamsemitted from one or more lasers, for example. In one example, theelectromagnetic radiation source (“source”) 11 could be a single devicethat can be configured to generate and emit a plurality ofelectromagnetic radiation beams with different wavelengths in sequenceor simultaneously, or that emits a single electromagnetic radiation beamwith multiple wavelength components. In another example, the source 11could be a set of individual sources, each configured to generate andemit electromagnetic radiation beams 22 with a desired wavelength. Theterm “source” can refer to a single source or multiple sources making upa source. In each case, the source 11 might generate a fixed wavelengthelectromagnetic radiation beam(s), or it might be tuneable to emit anelectromagnetic radiation beam(s) at one of a range of wavelengths.Other examples could be envisaged by those skilled in the art also.

Preferably, the source 11 is configured so that each electromagneticradiation beam 22 with a corresponding wavelength(s) can beindependently emitted in sequence. This might be achieved through usinga single source that is tuned to emit electromagnetic radiation beamsthat sweep through a range of wavelengths. Alternatively, where a sourcecomprises multiple electromagnetic radiation sources, each of which canbe operated in turn, it might be achieved by each source becoming the“active” source. So that the electromagnetic radiation beam of theactive source is directed along the desired sample path 14 a, eachelectromagnetic radiation beam output from the source can be arranged tohit a grating, mirror, prism or other optical apparatus 13 thatredirects the beam from that source along the desired sample path 14 a.In such arrangement, each electromagnetic radiation beam can be directedin sequence along the desired path as it is generated/activated.Alternatively, multiple electromagnetic radiation beams could besimultaneously directed along a beam path 14 a, resulting in a singlebeam of electromagnetic radiation comprising a plurality of wavelengthcomponents. Alternatively, the sources could be arranged on a carouselor linear carriage (also represented by 13) that can be mechanicallycontrolled to physically position each source to emit a radiation beamalong the path 14 a. These alternatives will be described further later.Other arrangements for redirecting a plurality of electromagneticradiation beams from a source 11 along a desired path 14 a could also beenvisaged. The electromagnetic radiation beam directed along the path 14a can be termed the sample electromagnetic radiation beam.

The apparatus 10 comprises a sample/sample retainer 16 for holding asample in the path 14 a of the sample electromagnetic radiation beam.The sample retainer 16 could be a test-tube/test-tube holder, other typeof test cell, part of an infusion pump/IV set, flow-cell, or any othertype of device for holding any of these or holding a sample/substance inany manner. The sample could alternatively simply be placed in the path14 a. Any sample retainer allows for transmission of the electromagneticradiation 22 to and through the sample. The sample is preferably aliquid based drug. The liquid based sample could, for example be a waterbased drug, but it could also be another type of sample/substance inwater or other liquid carrier. The term “sample” is used generally toindicate a substance for analysis (e.g. verification/identification) andis not necessarily restricted to a test sample/small portion of a largeramount of substance. For example, the sample could be an actual drug tobe administered—not simply a (sample) portion of that drug to beadministered. The apparatus 10 can be used in a clinical or otherenvironment to verify/identify a drug prior to admission. In this case,the sample put in the apparatus 10 will be the actual drug beingadministered.

An electromagnetic radiation beam emitted along the path 14 a providesincident electromagnetic radiation on a sample (substance) 16 placed inthe path (e.g. in the sample retainer.) Any incident electromagneticradiation beam 14 a that reaches the sample 16 is affected by the sample(e.g. either by transmission through and/or reflection by the sample.)The affected (sample) electromagnetic radiation 14 b that exits thesample 16 is affected electromagnetic radiation and contains spectralinformation regarding the sample. For example, the affectedelectromagnetic radiation 14 b comprises information about the intensityof the affected electromagnetic radiation at one wavelength of theincident radiation.

A sample detector 17 is placed in the affected electromagnetic radiationpath 14 b such that affected electromagnetic radiation 14 b exiting thesample can be detected. The detector 17 can comprise, for example, oneor more photodetectors. The detector 17 outputs information 14 c in theform of data/a signal that represents or indicates spectral informationof the sample 16—that is, the output represents the detected affectedelectromagnetic radiation. The detector 17 output is passed through to aprocessor 18 that carries out optionally a pre-processing and averification/identification algorithm in order to verify or identify orotherwise analyse the sample in the retainer. The processor 18 can fondpart of the controller 12, or can be separate thereto. The processor 18comprises or has access to a database 23 with reference/comparison datafor verifying or identifying or otherwise analysing the sample. The path14 a, 14 b, emitted and affected radiation and/or the sample/sampleholder 16 can be termed the “sample channel.” The sample detector 16 andinputs to the processor 18 (and optionally the processor itself) canalso form part of the sample channel.

Optionally there might also be a reference channel, in which the emittedelectromagnetic radiation beam 14 a incident on the sample 16 is split21 or otherwise redirected along a reference path 15 a towards anotherretainer 19 containing a reference sample/substance (or simply“reference”) 19. A beam splitter 21 could be used to achieve this. Thereference could be saline, for example. The reference sample retainer 19could be any one of those retainers 16 mentioned with respect to thesample channel. The reference electromagnetic radiation beam along thereference path 15 a is incident on and affected by the reference sample19 to produce affected (reference) electromagnetic radiation 15 b whichis incident on and detected by a reference detector 20. The referencedetector 20 could be the same or different detector to that of thesample channel. In FIG. 1, the reference detector 20 is shown as anindependent detector by way of example.

The reference detector 20 outputs information 15 c in the form of data/asignal that represents or indicates spectral information 15 c of thereference—that is, the output represents the detected affectedelectromagnetic radiation. The detector output 15 c is passed through tothe processor 18 that carries out pre-processing and averification/identification algorithm in order to verify or identify thesample 16 in the retainer. The detector output 15 c from the referencechannel provides data from which to normalise and/or correct the samplechannel data 14 c. The reference channel might also comprises a neutraldensity filter prior to the sample. This attenuates the incidentelectromagnetic radiation in a manner to normalise the detected affectedelectromagnetic radiation, or otherwise modify it so that the output ofthe detector is at a suitable level to enable processing/comparison withthe output of the detector on the sample channel.

Each electromagnetic radiation beam 22 has a wavelength (or has aplurality of wavelength components) that falls in the analysis range(“analysis region”), preferably of 1300-2000 nanometres (nm). Thisregion can nominally be termed “near infrared” or “NIR”. This regionprovides useful spectral information for verifying or identifying drugs.The wavelength of each electromagnetic radiation beam 22 (or thewavelengths making up an electromagnetic beam) is selected based onspectral characteristics (features) of the base liquid of the drugsample that fall within the analysis range. Such characteristics couldbe, for example, peaks, troughs, points of inflection, stable point orregions, plateaus, knees and/or slopes of that base liquid spectrum.Each wavelength selected is in the vicinity of (or within a regionspanning) such a spectral characteristic. The position of a spectralcharacteristic could be defined by a nominal wavelength (of for examplethe centre wavelength of the characteristic) or a range of wavelengthsdefining a region spanning the characteristic.

Selection of each wavelength can be demonstrated with reference to thespectrum of a hypothetical base liquid as shown in FIG. 2. Thehypothetical spectrum comprises the following spectral characteristicsA-E in the analysis range.

-   -   A peak between 1300 nm and 1400 nm (centre wavelength of 1350 nm        of actual peak) (A).    -   A trough between 1400 nm and 1500 nm (centre wavelength of 1450        nm of actual trough) (B).    -   An inflection between 1500 nm and 1600 nm (centre wavelength of        1550 of actual inflection) (C).    -   A slope between 1600 nm and 1800 nm (D).    -   A plateau between 1800 nm and 2000 nm (E).    -   A knee is also shown around 1800 nm between characteristics D        and E.

For analysis of drugs with this hypothetical liquid as a base,wavelengths could be chosen that are within the vicinity of thewavelength ranges (or centre wavelength) for one or more of the spectralfeatures A-E above, or that fall within in a region spanning(defining/delimiting) the wavelength ranges for one or more of thespectral features A-E above. A wavelength in the “vicinity” of aspectral characteristic also can mean a wavelength at the spectralcharacteristic centre wavelength. For example, three differentwavelengths could be chosen as follows.

-   -   Wavelength #1 1310 nm—within the region 1300-1400 nm for feature        A.    -   Wavelength #2 1450 nm, roughly at or within the vicinity of the        centre wavelength of feature B.    -   Wavelength #3 1800 nm, at the edge/knee (i.e. within the region)        of feature E.

The chosen discrete wavelengths that relate to spectral characteristicsof the liquid spectrum can be termed “selected wavelengths” or “chosenwavelengths”. In general terms, the selected or chosen wavelengths“correspond” to or “capture” a spectral characteristic.

It will be appreciated that FIG. 2 shows just some hypothetical examplesof spectral characteristics (features)—many more are possible for aspectrum. Further, the wavelength ranges for spectral characteristicscould overlap or even coincide. Further, a separate wavelength need notbe chosen for each spectral characteristic in the analysis range—just aselection of wavelengths relating to a selection of spectralcharacteristics might be chosen. It might not be possible to define aspectral characteristic by a wavelength range, or any such range mightvary depending on interpretation. A wavelength in the vicinity of aspectral characteristic might instead be chosen. This could be awavelength that is near or within a certain tolerance (e.g. +/−30 nm) ofthe centre point wavelength of a spectral characteristic, for example.

In addition, the selected wavelength might be influenced by sources 11that are readily obtainable or configurable to a wavelength that is inthe vicinity of or falls within in a region spanning such a spectralcharacteristic. The selection of suitable wavelengths for the emittedradiation will provide better information for accurate verification oridentification by the processor.

In addition, preferably, the selected wavelengths can be selectedindependently from the drug(s) being tested.

Any suitable number of wavelengths can be used. Optionally, although notessentially, the number of different wavelengths constituting theelectromagnetic radiation (either in one or multiple beams 22) providedby the source 11 is at least log₂ n, where n is the number of samplesthat are tested for. The more wavelengths that are used, the better theaccuracy, but this is optimised against costs and convenience. As seenin FIG. 3, as the number of electromagnetic radiation beams/wavelengthsincreases, the error of detection decreases. A selection of twowavelengths provides an error of 0.14 for a set of 30 drugs, whereasfive wavelengths provide an error of just 0.02.

One of the electromagnetic radiation wavelengths 22 can be selected tohave a wavelength at an anchor point, which can be used to eliminate theneed for a reference channel. The anchor point is chosen to have awavelength in a stable or other suitable portion of the spectrum of theunderlying base liquid. The anchor wavelength is described furtherlater.

Upon receiving output from a sample detector 17 and optionally areference detector 20, the processor 18 executes an algorithm thataccesses a database 23 comprising comparison data, and uses that outputto verify or identify the sample 16 based on the affectedelectromagnetic radiation 14 b detected from the sample 16, andoptionally where a reference channel is used, the detected affectedradiation 15 b from that reference sample using the comparison data. Theprocessor 18 can operate with or independently from the controller 12.Processing will be described further later.

A user interface 24 allows a user to operate the apparatus 10, includingsetting parameters, inputting anticipated drugs and receiving theresults of analysis (via a screen, display, audio alarm, indicator orsimilar). The results might indicate whether the drug is as anticipated(verification/confirmation), or might advise of the drug(identification).

Preferably, the apparatus 10 also comprises a feedback system tostabilise the temperature of the electromagnetic radiation source 11and/or the detectors(s) 17, 20. In one example, thermistors detect thetemperature of the electromagnetic radiation source and/or detector(s).Peltier cooling devices can be operated to cool and stabilise thetemperate of the source 11 and detectors 17, 20. The output of thethermistor(s) is sent to the controller 12, which controls the peltiercooling devices to cool the source and/or detectors. Preferably thethermistor is the built-in photodetector thermistor 5 a, 5 b. And thepeltier thermo-electric cooler is built-in to the photodetector 5 a, 5b.

The apparatus 10 works generally as follows, with reference to the flowdiagram in FIG. 4. The controller 12 is used to operate the source 11 toemit one or more electromagnetic radiation beams 22 (preferablyindividually and in sequence) with/at the selected wavelengths towardsthe sample 16, step 40. The electromagnetic radiation incident 14 a on asample 16 is transmitted or reflected through the sample and becomesaffected electromagnetic radiation 14 b which is detected by thedetector 17, step 41. Optionally, the emitted radiation maybe divertedby a beam splitter 21 also to a reference sample 19, which is detectedby the same or a different detector 20, step 42. The outputs 14 c, 15 cfrom the sample detector 17 and optionally the reference detector 20 arepassed to the processor 18, step 42. Here pre-processing takes place tonormalise and/or correct the detector output 14 c, 15 c, step 42. Thenthe identification/verification algorithm is executed, step 43, whichincludes querying the database 23 of reference drugs, the informationfrom which being utilised to identify or verify the sample from thenormalised detector output. The result of the verification oridentification of the sample is communicated by the user interface 24,step 44.

Other options will become apparent as a more detailed description of theinvention is provided.

First Embodiment

One possible embodiment of the invention will now be described in detailby way of example. This should not be considered limiting butillustrative. The embodiment is described in relation to an apparatusfor providing verification or identification of water based drugs frome.g. a set of 30 drugs.

Six wavelengths of electromagnetic radiation are chosen for thisexample, six being greater than log₂ n of 30. The wavelengths are chosenin the analysis range and are based on the spectral characteristics ofwater, being the base liquid, falling in that range. The spectrum of awater based drug (or other liquid based drug or aqueous solution) willbe heavily dominated by the base liquid spectrum. For example referringto FIG. 5, the spectrum (dotted line) of drug W (gelofusine succinatedgelatine solution 4%) is very similar to the spectrum of water (solidline). This is because the spectrum of water dominates. However, thedifferences in transmission coefficient between different water baseddrugs can be measured. Focussing on areas/wavelengths of spectralcharacteristics of the water spectrum, by using electromagneticradiation beams at those wavelengths, the difference between the waterspectrum and the water based drug spectrum at those wavelengths can beutilised to provide drug discrimination for drug identification orverification.

FIG. 6 shows a spectrum of water with some possible spectralcharacteristics (features) in the analysis range identified, andexplained further below.

-   -   Spectral characteristic A (slope)—in a first region between 1300        nm and 1400 nm.    -   Spectral characteristic B (plateau/trough)—in a second region        between 1400 nm and 1500 nm.    -   Spectral characteristic C (slope)—in a third region between 1500        nm and 1600 nm.    -   Spectral characteristic D (peak)—in a fourth region between 1600        nm and 1700 nm.    -   Spectral characteristic E (inflection)—in a fifth region between        1700 nm and 1800 nm.    -   Spectral characteristic F (knee) a sixth region between 1800 nm        and 2000 nm.        This is not an exhaustive list of possible spectral features.

The selection of a wavelength for an electromagnetic radiation beam isnot strictly fixed, and not necessarily solely based on spectralcharacteristics of the base liquid. It is influenced by the wavelengthof spectral characteristics in spectrum of the base water of the drugsample, but in addition the selected wavelength can be based on otherfactors also. For example, in interest of cost effectiveness and aregularly obtainable supply chain, it might be preferable to use orselect an alternative wavelength that is close to the spectralcharacteristic but not quite the same, if that alternative wavelength iseasily obtainable by an off-the-shelf laser or other optical component.

For example, it is possible to use 1310 and 1550 nm as selectedwavelengths for water based drugs as there are many devices configuredfor these wavelengths as they have wide spread use within thecommunications industry. Laser diodes nominally have centred wavelengthsat 1650 nanometres, 1750 nanometres and 1850 nanometres, although these,can be varied by up to plus or minus 30 nanometres. So wavelengths inthese ranges can also be selected. Therefore by looking at theavailability of these components, and the spectral characteristics ofthe base liquid, suitable wavelengths for the emitted radiation can bedetermined.

Therefore, based on the above explanation, each of the six wavelengthscan be chosen to be within the vicinity or within the region spanningone of each of the spectral features, but also influenced by theavailability of hardware. The six wavelengths for water could thereforebe (by way of example): 1350 nanometres corresponding to feature A, 1450nanometres corresponding to feature B, 1550 nanometres corresponding tofeature C, 1650 nanometres corresponding to feature D, 1750 nanometrescorresponding to feature E and 1850 nanometres corresponding to featureF, all which fall within the 1300-2000 nanometres. As can be seen the1350 nm to 1850 nm wavelength selections do not match exactly to peaksand troughs and other spectral characteristics in the water spectrum,although are close. The selections also relate to operating wavelengthsof available hardware. These are of course nominal wavelengths and theactual wavelength might vary in practice due to source 11characteristics.

FIG. 7 shows in schematic form one possible form of the apparatus 10 asgenerally described in FIG. 1. The spectroscopic analyser 10 has acontroller 12 and a carousel 50 that supports six lasers 51 a-51 f,which together form the source 11 to output electromagnetic radiation 22at a plurality of wavelengths in the form of light. Each laser is tunedor tuneable to emit electromagnetic radiation 22 at one of the sixwavelengths defined above. Each laser can comprise or be formed fromlaser diodes providing a stable, high intensity, narrow band collimatedelectromagnetic radiation output that is readily controlledelectronically via driver circuitry. Each laser comprises a lens thatcan collimate the emitted electromagnetic radiation 14 a into a beamusing appropriate lenses. Each laser 51 a-51 f can have one or morephotodiodes 4 a-4 f for detecting output electromagnetic radiation forfeedback control of that radiation. Lasers have fewer heat emissionproblems than other sources, thus reducing the detrimental effects ofheat on the measurements. The output power of each laser preferably isnominally the same (typically 30 mW) in the interests of having abalanced apparatus. Preferably, this also enables a common diode drivercircuit to be used for the laser diodes.

The controller 12 can control the carousel 50 to rotate about an axis toactivate any one of the lasers 51 a-51 f in turn and align the activatedlaser (e.g. 51 f as shown) to emit a beam 22 along the sample path/beampath 14 a. The lasers 51 a-51 f can also be turned off completely tofacilitate the measurement of dark current signals if required. The useof mechanically activated optical chopper can thereby be eliminated(although one can be included if desired.) Once activated, the laseremits electromagnetic radiation 22 towards the sample along the path 14a. The path 14 a from the source to the detector is preferablypredominantly via free-space preferably with minimal if any opticalfibre components. This reduces optical attenuation and hardware. Theapparatus also comprises a sample retainer 16 a, which is aligned withthe beam path 14 a. The emitted electromagnetic radiation from an activelaser 51 a-51 f is incident on and transmits or reflects through thesample 16 in the sample retainer.

The detector 16 is placed in the affected radiation path 14 b that exitsthe sample 16 a. Preferably the detector 16 is a singlephotodetector/photodiode biased to have a suitable response to detectelectromagnetic radiation of wavelengths that will be in the affectedradiation. A single detector reduces the errors due to variabilityintroduced by components—it removes the relative differences betweenmultiple photodetectors enabling a more stable response to the output ofthe emitted electromagnetic radiation thus enhancing sensitivity. AnInGaAs photodiode could be used, for example. The detector 17 detectsthe affected radiation 14 b and the output 14 c of the detector 17 ispassed to a processor 18 that verifies or identifies the sample asdescribed above.

The apparatus also has a beam splitter 21 to redirect the incidentelectromagnetic radiation beam 22/14 a towards a reference sampleretainer along a reference path 15 a, which passes through to areference detector 20. The output of the reference detector 20 is alsopassed to the processor 18. The reference could be saline, for example.

Preferably, the apparatus also comprises a feedback system to stabilisethe temperature of the electromagnetic radiation source 11 and thedetectors(s). In one example, thermistors detect the temperature of theelectromagnetic radiation source and/or detector(s). Peltier coolingdevices can be operated to cool and stabilise the temperate of thesource and detectors. The output of the thermistor(s) is sent to thecontroller, which controls the peltier cooling devices to cool thesource and/or detectors. Preferably the thermistor is the built-inphotodetector thermistor 5 a, 5 b. And the peltier thermo-electriccooler is built-in to the photodetector 5 a, 5 b.

Referring to FIG. 4, operation of the apparatus 10 will now bedescribed. The controller 12 operates the carousel 50 to rotate eachlaser 51 a-51 f in turn to the activate position. When in the activateposition, the laser 51 a-51 f is operated by the controller 12 to emitan electromagnetic radiation beam at one of the selected wavelengths tothe sample 16 (and optionally to reference sample 19.) In this manner,six electromagnetic radiation beams with different selected wavelengthsare emitted, step 40, in sequence from each of the six lasers 51 a-51 f,each tuned to a different selected wavelength. Each laser 51 a-51 f inturn emits an electromagnetic beam 22 along the path 14 a towards thesample. The affected radiation coming from the sample is detected, step41, for each electromagnetic radiation beam emitted 14 a towards thesample 16. The electromagnetic radiation beam could be switched on andoff to get a reading/measurement made by the detector during the offphase also—this can give a dark signal/current for reference purposes.The emitted electromagnetic radiation is also directed along thereference path 15 a, through the reference sample 19 using the beamsplitter 21, and detected by the reference detector 20. The outputs fromthe sample detector 17 and the reference detector 20 are passed to theprocessor 18, step 42. The processor (optionally) carries outpre-processing on the output from the detectors, and then verifies oridentifies the drug based on the pre-processed outputs, step 43. Itoutputs the results via the user interface 24, step 44.

In one possible embodiment, the processor 18 comprises or implements apre-processing method and then a verification/identification method asshown in FIG. 8. In this embodiment a reference channel is used and alsodark current readings. Dark current is the output provided by thedetectors 17, 20 when no electromagnetic radiation (e.g. light) isincident on them. This dark current reading from the detector can besubtracted from the actual reading from the detectors for calibrationpurposes. Having a dark reading is not essential for the invention andis described here as one possible option—the remaining description ofthe processing method would work also without dark readings being takenor by.

Prior to carrying out the verification or identification in FIG. 8, atraining process is carried out to produce a comparison data from whichsamples can be verified/identified as shown in FIGS. 9-11. In thetraining process, an algorithm is used to generate the comparison data,which determines the particular linear combination of data values fromeach of the sample data that optimises the separation between differentdrugs. The resulting mathematical rule is then applied to the dataacquired for the drug under test to verify that it is the intended drug.In the embodiment described, dark current readings are used. Thetraining process preferably comprises a pre-processing stage, and acomparison data generation stage. Pre-processing is not essential, butimproves performance.

Referring to FIG. 9, for the training process, a number of trainingsamples are tested in the analyser in turn. Each training sample relatesto a sample that will be test for during actual use of the analyser. Foreach training sample, output from both sample and reference channels isreceived at the processor, step 90. If dark current is being used, theoutput from each detector for the dark reading is subtracted from theoutput of the actual reading. The output 14 c received at the processor18 from the sample detector 17 indicates the intensity of the affectedelectromagnetic radiation 14 b for each emitted electromagneticradiation beam at the sample 16. It may, for example, comprise datawhich directly or indirectly indicates photocurrent of the detectorand/or intensity of the detected electromagnetic radiation. Likewise,the output 15 c received at the processor 18 from the reference detector20 indicates the intensity of the affected electromagnetic radiation 15b for each emitted electromagnetic radiation beam at the referencesample. Preferably, the apparatus carries out multiple measurements foreach wavelength. For example, at each wavelength, the apparatus detectsaffected electromagnetic radiation affected by the sample at 15different times and passes this output to the processor, step 94.Similarly, at each wavelength, the apparatus detects affectedelectromagnetic radiation affected by the reference at 15 differenttimes and passes this output to the processor, step 94.

Next, for each wavelength, the processor 18 generates from the output ofthe reference and sample detectors a range of sample data points for thesample that correlate an intensity of affected electromagnetic radiation14 b affected by the sample at a particular selected wavelength, step91. These data points 100 could be plotted, as shown for example in FIG.10—although it will be appreciated that the processor does notnecessarily actually plot the data. The x axis shows intensityindicative values corresponding to detector output for the sampledetector 17, and the y axis shows intensity indicative valuescorrelating to detector output for the reference detector 20. The valuesindicate directly or indirectly the intensity of detected affectedelectromagnetic radiation. Where a reference channel is used, output onthe reference detector is paired with output from the sample detectortaken at the same time. Each sample/reference channel detector outputvalue pair is plotted on the graph. Such measurements can be taken forseveral times for each wavelength. Therefore, the plot in FIG. 10 showsthe values indicative of intensity 103 measured at several times (e.g.15) for a particular selected wavelength (e.g. nominally 1350 nm) ofelectromagnetic radiation incident 14 a on the training sample 16 and onthe reference 19.

For each training sample, the process is then repeated to get similardata points for a second (comparison) sample 101 and a control (e.g.saline) 102. The sample/reference channel detector output value pairsfor the second (comparison) 101 sample and control sample 102 could alsoplotted on the graph, as shown in FIG. 9, step 91.

A best fit straight line can then be calculated using a suitablestatistical technique, step 92, and the intercept value of the x axis isfound, step 92, for each of the:

-   -   training sample set, 103    -   second (comparison) sample 101, and the    -   control sample 102        set of data points for the particular wavelength (1350 nm), as        shown in FIG. 10.

From this a normalised pre-processed value is found. For example, thex-axis intercept values (e.g. 842500 and 850500) for the training sample103 and control 102 respectively can be found, and then can besubtracted from each other to obtain normalised pre-processed values(e.g. 8000), step 93. Similarly, the x-axis intercept values (e.g. 86000and 850500) for the second (comparison) sample 101 and control 102respectively can be found also, and then subtracted from each other toobtain normalised pre-processed values (e.g. 95000), step 93. Thisprocess can be carried out for each of the other selected wavelengths(e.g. five others in this case), step 94 and steps 90-93, resulting in aset of six normalised pre-processed values (—one for each wavelength)for the training sample. The process can also be carried out for each ofthe other selected wavelengths for the second (comparison) sample,resulting in a set of six normalised pre-processed values for the second(comparison) drug for each wavelength. These sets of normalisedpre-processed values for the training sample and second (comparison) foreach wavelength sample can be correlated/plotted in a multidimensionalspace, each axis corresponding to a wavelength and the pre-processedvalue for that wavelength being plotted relative to that axis.

In practice, this process, steps 90-94, can then be carried out numeroustimes for each wavelength, so that for each training sample and second(comparison) sample, there are a plurality of sets of six normalisedpre-processed values. Each set can be plotted/correlated as one point ina multidimensional (six dimensions in this case) space. An example ofsuch a plot is shown in FIG. 11. Here, for simplicity, only a twodimensional space is shown, each axis relating to the results from twowavelengths—in reality it would need to be a six-dimensional graph tocover all six wavelengths. For each set for each of the training sampleand second (comparison) sample, a pair of two normalised pre-processedvalue (i.e. one value for each wavelength) is plotted as a single pointon the two dimensional graph, e.g. 110, resulting in a normalisedpre-processed value data set for the training sample 111 and the second(comparison) sample 112.

The pre-processing stage described above reduces the detrimental effectsof systematic errors in the system and drift in the measured data. Note,the reference channel/value is optional. In an alternative, x-axisintercept values are found for the sample data only.

In an alternative embodiment, the pre-processing steps previouslydescribed can be omitted on the grounds that system drift and systematicerrors can be virtually eliminated with the use of highly stable laserdiode sources and a reference signal derived from the laser's ownmonitor diode output. This facilitates the use of a single channel witha single photo-detector eliminating the need for separate opticalreference channel and/or control sample to be used. To this end, thedata base of measured transmission spectra for a range of intravenousdrugs can be built up in a more straightforward manner by sequentiallymeasuring samples of each drug in a single channel using multiple testtubes.

After the data has been pre-processed for the training sample and second(comparison) sample and correlated as shown in FIG. 11, a representativevalue can be obtained for the training sample. If no pre-processing iscarried out, the process proceeds to finding the representative value onnon-pre-processed (raw) data. First a line 113 that separates thetraining sample data set 111 from the second (comparison) sample dataset 112 is determined, step 95. Then the normal direction of the line isused as a weighting in a score to separate the training sample from thecomparison sample. Also, a threshold is determined below which thetraining sample falls, step 96. The threshold and weighting scoreprovide a representative value for comparison data to assist inverification/identification for that training sample. The representativevalue is stored as comparison data in a database 23 for the trainingsample, step 98.

The entire process is the repeated (step 99, and steps 90-98) for thesame training sample against a third (comparison) sample to get a secondrepresentative value for storing as comparison data in the database 23for the training sample. Then the process is repeated again (step 99,and steps 90-98) against a fourth and subsequent comparison samples togenerated a third and subsequent representative values for storing ascomparison data for the training sample. Together these form therepresentative values in the comparison database to identify/verify thetraining sample.

The entire process (step 100, step 90-99) is the repeated for each othertraining sample (in the set of n drugs) against multiple comparisonsamples, in order to obtain representative values for each additionaltraining sample also.

It will be appreciated that in describing the training process steps90-100, there has been reference to graphs and techniques. These aredescribed for illustrative purposes. Any processor carrying out thetraining process to determine representative values might not actuallyproduce such graphs or utilise such techniques to obtain the end result,but rather use other processing techniques that achieve the same result.

The above training process will generate comparison data for eachtraining sample (in the set of n drugs) that can stored in the database23 and can be used to identify or verify actual samples from the setunder test. The comparison database 23 can be generated well in advanceof actual sample testing, or can be generated soon before or evenon-the-fly. The comparison data can be considered as a multidimensionalverification/identification matrix based on the acquiredmultidimensional spectral data from the detectors. The comparison datacan be used to verify or identify any of the drugs from any of the otherdrugs in the set of n drugs.

Referring back to FIG. 8, once a comparison database is produced andstored in the database 23, verification/identification of actual samplesoccurs as follows. Output from both sample and reference channels isreceived at the processor, step 80. If dark current is being used, theoutput from each detector for the dark reading is subtracted from theoutput of the actual reading. The output 14 c received at the processor18 from the sample detector 17 indicates the intensity of the affectedelectromagnetic radiation 14 b for each emitted electromagneticradiation beam at the sample 16. It may, for example, comprise datawhich directly or indirectly indicates photocurrent of the detectorand/or intensity of the detected electromagnetic radiation. Likewise,the output 15 c received at the processor 18 from the reference detector20 indicates the intensity of the affected electromagnetic radiation 15b for each emitted electromagnetic radiation beam at the referencesample. Preferably, the apparatus carries out multiple measurements foreach wavelength. For example, at each wavelength, the apparatus detectsaffected electromagnetic radiation affected by the sample at 15different times and passes this output to the processor, step 80.Similarly, at each wavelength, the apparatus detects affectedelectromagnetic radiation affected by the reference at 15 differenttimes and passes this output to the processor, step 80.

This output is then preferably pre-processed, steps 81-84, in the samemanner as described above for the training process and with reference toFIGS. 9 to 11. That description need not be repeated here, but insummary, data points are generated, step 81, best fit lines found, step82, and x-axis values are obtained which provide normalisedpre-processed values, step 83. This is done for all wavelengths, step84. Pre-processing is not essential, but can improve performance.

After this pre-processing is carried out for the affected radiation ofeach wavelength, steps 81-84, the identification/verification algorithmcan then be invoked, step 85. Verification involves confirming that asample drug is the drug that is expected. For example, a clinician canspecify what they think the drug is (e.g. from the set of n drugs)through the user interface 24, e.g. step 80, then use the apparatus toconfirm whether the drug in the retainer is actually that drug which isspecified by the clinician. Identification involves determining what adrug actually is, without any suggestion from the clinician as to whatthe drug is. For verification/identification, the spectral data (thatis, the pre-processed values) are compared against the comparison datain the database 23, step 85, to identify the drug, or verify whether itis the anticipated drug as specified by the clinician. Output is thenprovided to the user interface, step 86.

In one possible identification/verification algorithm, once the sampledata is obtained and pre-processed, representative values are found forthe sample, in the same manner that they were found during the trainingprocess as explained with reference to FIGS. 9 to 11. The representativevalues are found for the sample at each selected wavelength and withrespect to each other comparison sample. The representative values arecompared to the representative values in the comparison data. If thereis sufficient similarity between the representative values found for thesample and the representative values in the comparison datacorresponding to the same sample, then verification or identification ismade. Sufficient similarity can be determined using any suitablestatistical or other technique. For example, sufficient similarity mightoccur when some or all of the representative values match those in theverification matrix. In another example, this might occur when thesample falls below the threshold for each comparison sample. An alarm oroutput might be made via a user interface to advise the user of theresult of the verification/identification.

FIG. 15 shows test data for a set of 30 drugs verified using theanalyser. In the test, each drug was inserted in the analyser, and thensystematically the analyser was configured to check if it was one of the30 drugs. If an alarm was raised, this indicated the drug was not theone that was anticipated, and the alarm noted. Each drug was tested 15times, in relation to each of the other drugs. So, for example,Metaraminol was put into the analyser and then the analyser wasconfigured to check for Metaraminol. After 15 tests, the analyser didnot once raise an alarm, indicating that the analyser did not detectMetaraminol as another drug. Keeping Metaraminol in the sample retainer,the analyser was then configured to check for Heparin. For each of 15independent tests, the analyser raised an alarm, indicating it detectedeach time that the drug in the analyser (Metaraminol) was not the drugit was expecting (Heparin). The analyser was then reconfigured for eachof the other drugs, and the test done 15 times for each, whileMetaraminol was in the sample retainer. The same process was thenrepeated for every other drug being used as a sample, with the analysersystematically being re-configured to check for every other drug. Eachtime an alarm was raised (indicating the analyser did not consider thedrug in the retainer was that being checked form), the alarm was noted.The table in FIG. 15 reflects the number of times an alarm was raised ofeach drug detection combination. The error rates are shown. The lowerror rates demonstrate a significant improvement in verificationaccuracy.

Second Embodiment

FIG. 12 shows an alternative embodiment of the apparatus 10. In thisembodiment rather than using a carousel 50, the six lasers 51 a-51 fforming the source 11 are arranged to emit their electromagneticradiation beam 22 towards a diffraction grating 120 of the reflectiontype. Each laser 51 a-51 f is operable to emit a tuned or tuneablewavelength of a collimated electromagnetic beam 22 towards thediffraction grating. The angle of incidence X on the grating surface foreach laser 51 a-51 f is chosen that their first order diffracted beamemerges at the same angle Y thereby producing a common optical path 14 afor each laser. The controller 12 activates each laser 51 a-51 fsequentially to emit a beam of a single wavelength towards the sample.Alternatively, multiple lasers 51 a-51 f could be operated at once suchthat an electromagnetic beam 22 comprising multiple wavelengthcomponents could be emitted towards the sample 16. A separate grating orbeam splitter 21 could be used for example as shown in FIG. 1 to directthe beam towards a reference channel sample 19, if there is one. Allother aspects of the embodiment can be as shown and described in FIGS.1, 2, 16 and/or 18.

Third Embodiment

FIG. 13 shows another alternative embodiment of the apparatus 10. Inthis embodiment rather than using a carousel 50, the six lasers 51 a-51f forming the source 11 are arranged to emit their electromagneticradiation beam 14 a towards respective beam splitters 130 a-130 f thatredirect the emitted electromagnetic radiation beam 22 along the samplepath 14 a. The controller 12 can control each electromagnetic radiationsource 11 in turn to emit a tune or tuneable wavelength ofelectromagnetic radiation towards the sample via the respective beamsplitter 130 a-130 f. Alternatively, two or more of the lasers 51 a-51 fcould be activated at once to provide an electromagnetic beam 22 withmultiple wavelength components towards 14 a the sample 16. An absorber135 is provided behind the beam splitter array to mop up transmittedenergy from the beam splitters. A separate grating or beam splitter 21could be used for example as shown in FIG. 1 to direct the beam towardsa reference channel sample 19, if there is one. All other aspects of theembodiment can be as shown and described in FIGS. 1, 2, 16 and/or 18.

Fourth Embodiment

FIG. 14 shows an alternative embodiment of the apparatus 10. In thisembodiment rather than using a carousel 50, the six lasers 51 a-51 fforming the source 11 are arranged to emit their electromagneticradiation beam 22 towards a prism 140. Each laser 51 a-51 f is operableto emit a tuned or tuneable wavelength of a collimated electromagneticbeam 14 a towards the prism. The angle of incidence X on the gratingsurface for each laser 51 a-51 f is chosen that their first orderrefracted beam 22 emerges 14 a at the same angle Y thereby producing acommon optical path 14 a for each laser 51 a-51 f. The controller 12activates each laser 51 a-51 f sequentially to emit a beam of a singlewavelength towards the sample. Alternatively, multiple lasers 51 a-51 fcould be operated at once such that an electromagnetic beam 22comprising multiple wavelength components could be emitted towards 14 athe sample 16. A separate grating or beam splitter 21 could be used forexample as shown in FIG. 1 to direct the beam towards a referencechannel sample 19, if there is one. All other aspects of the embodimentcan be as shown and described in FIGS. 1, 2, 16 and/or 18.

Fifth Embodiment

FIG. 20 shows an alternative embodiment of the apparatus 10. In thisembodiment rather than using a carousel 50, the six lasers 51 a-51 fforming the source 11 are arranged to emit their electromagneticradiation beam 22 through separate fibre optic cables 201 a-201 ftowards a planar lightwave circuit (PLC) (fibre optic combiner) 200.Each laser 51 a-51 f is operable to emit a tuned or tuneable wavelengthof a collimated electromagnetic beam 14 a towards the PLC 200 via thefibre optic cables 201 a-201 f. The controller 12 activates each laser51 a-51 f sequentially to emit a beam of a single wavelength towards thesample. Alternatively, multiple lasers 51 a-51 f could be operated atonce such that an electromagnetic beam 22 comprising multiple wavelengthcomponents could be emitted towards 14 a the sample 16. A separategrating or beam splitter 21 could be used for example as shown in FIG. 1to direct the beam towards a reference channel sample 19, if there isone. All other aspects of the embodiment can be as shown and describedin FIGS. 1, 2, 16 and/or 18.

Sixth Embodiment

FIG. 21 shows an alternative embodiment of the apparatus 10. In thisembodiment rather than using a carousel 50, a single package 211comprising 6 lasers forming the source 11 are arranged to emit theirelectromagnetic radiation beam 201 a-201 f towards an integratedcollimating lens 210. The laser is operable to emit a tuned or tuneablewavelength at each of 6 wavelengths towards the lens 210. The controller12 activates the laser to sequentially to emit a beam 212 a-212 f of asingle wavelength towards the sample. Alternatively, multiple beams 51a-51 f could be operated at once such that an electromagnetic beam 22comprising multiple wavelength components could be emitted towards 14 athe sample 16 via the lens 210. A separate grating or beam splitter 21could be used for example as shown in FIG. 1 to direct the beam towardsa reference channel sample 19, if there is one. All other aspects of theembodiment can be as shown and described in FIGS. 1, 2, 16 and/or 18.

Alternative Embodiments

The nominal analysis range of 1300-2000 nm for selected wavelengths ischosen as it provides advantages for improved drug verification oridentification. However, it will be appreciated that the reference to1300-2000 nm should not be considered limiting, and wavelengths could bechosen that relate spectral characteristics in slightly different rangesor other ranges entirely. The selected wavelengths (and therefore thespectral characteristics) fall within any analysis range provide forimproved identification/verification for drugs in the liquid carrier.For example, the analysis range could be a subset of 1300 nm-2000 nm,such as 1300 nm-1900 nm; 1350 nm-1950 nm; 1400 nm-1900 nm; 1500 nm-1800nm or some other subset. The range could also be larger, such as1250-2050 nm; 1200 nm-2100 nm; or 1150 nm-2150 nm or the like. Theanalysis range might even be offset from the nominal range, such as 1200nm-1900 nm, or 1300 nm-1900 nm. These are non-limiting examples. Ingeneral, the analysis range could start, for example, anywhere from 1100nm-1500 nm and end anywhere from 1800 nm-2150 nm. Even that isnon-limiting and the range could be something different entirely thatprovides for improved verification/identification. Further, wavelengthsfalling outside these analysis ranges and corresponding to spectralfeatures lying outside these analysis ranges above could also be used incombination with wavelengths falling in the analysis ranges mentioned.Using a plurality of wavelengths corresponding to spectralcharacteristics falling within the analysis range provides improvedperformance. Preferably any and all wavelengths are selected within theanalysis range, but that does not preclude using wavelengths falling inother ranges also where that might be useful.

The range could be at least partially influenced by component selection.For example, silicon photodiodes have a response down to at least 1100nm, so if used this wavelength might be used as the bottom end of therange. Preferably, the invention uses only one detector, so the rangemight be defined by what a single detector can cover—for example 1300nm-2000 nm in the case of an InGaAs detector.

Other liquids to water might have other analysis ranges that provideimproved identification/verification.

In an embodiment described above, a dark current was used tocalibrate/normalise the output data from the detectors 17, 20. The darkcurrent is subtracted from the detector reading. In another embodiment,obtaining dark current readings using a chopper wheel (or turning off ofthe source 11) is not required. Rather, laser driver current modulationis used to eliminate the need for dark current readings. Referring tothe simplified schematic of the analyser in FIG. 16, the laser is drivenby a driver current/modulator 160. The driver current/modulator may faunpart of the source or be separate to it. The source 11 is a laser diodewith built-in photodetector 4 (to provide control feedback). A samplecell 16 and photodetector 17 are provided. The laser driver currentmodulator 160 is also shown in FIG. 18 incorporated into the moredetailed block diagram of the overall analyser in FIG. 1.

The sample channel output current is the sum of two components—a darkcurrent term that is present even in the absence of any illumination,and a term proportional to the intensity of light incident on thedetector. Therefore, we can write the sample channel output current,I_(S) as follows:I _(S) =I _(S) ^(Dark) +S·P  (1)where in (1):

-   I_(S) ^(Dark) is the dark current signal of the sample channel    detector-   S is a constant representing the attenuation in the optical path    including the sample cell.-   P is the incident power illuminating the sample cell.

A similar expression can be written for the reference channel outputcurrent, I_(R), generated from the built-in photo-detector of the laserdiode source, namely:I _(R) =I _(R) ^(Dark) +R·P  (2)where in (2):

-   I_(R) ^(Dark) is the dark current signal of the reference    photo-detector in the laser diode package.-   R is a constant representing the fraction of incident power    delivered to the reference.

We now excite the laser source by modulating the driver current with aknown waveform. Typically, a sinusoidal modulation with angularfrequency ω is used to vary the current about a mean value. This has theeffect of modulating the output power of the laser diode source in asimilar sinusoidal manner illustrated in FIG. 17.

Mathematically, the time-dependent laser output power, P(t), can bewritten as follows:P(t)=P ₀ +ΔP·sin(ωt+ϕ)  (3)where in (3):

-   P₀ is the mean output power from the laser-   ΔP is the modulation amplitude in the output power waveform (depth    of modulation)-   ϕ is the phase of the modulation waveform at tine, t=0.

If we now substitute for the incident power in equations (1) and (2)using (3), we obtain the following expressions for the output currentsfrom sample and reference channels:I _(S) =I _(S) ^(Dark) +S·P ₀ +S·ΔP·sin(ωt+ϕ)I _(R) =I _(R) ^(Dark) +R·P ₀ +R·ΔP·sin(ωt+ϕ)

The parameters of interest with respect to characterising the sampleunder test are the constants S and R. The ratio of these two constantsrepresents a normalised coefficient characteristic of the liquid in thesample cell.

Expanding the sinusoidal term in the above equations, gives:sin(ωt+ϕ)=sin(ωt)cos ϕ+cos(ωt)sin ϕwhich gives the following:

$\begin{matrix}\begin{matrix}{I_{S} = {I_{S}^{Dark} + {S \cdot P_{0}} + {{S \cdot \Delta}\;{P \cdot {\sin\left( {\omega\; t} \right)}}\cos\;\phi} + {{S \cdot \Delta}\;{P \cdot {\cos\left( {\omega\; t} \right)}}\sin\;\phi}}} \\{\equiv {A_{0S} + {A_{1S}{\cos\left( {\omega\; t} \right)}} + {B_{1S}{\sin\left( {\omega\; t} \right)}}}}\end{matrix} & (4) \\\begin{matrix}{I_{R} = {I_{R}^{Dark} + {R \cdot P_{0}} + {{R \cdot \Delta}\;{P \cdot {\sin\left( {\omega\; t} \right)}}\cos\;\phi} + {{R \cdot \Delta}\;{P \cdot {\cos\left( {\omega\; t} \right)}}\sin\;\phi}}} \\{\equiv {A_{0R} + {A_{1R}{\cos\left( {\omega\; t} \right)}} + {B_{1R}{\sin\left( {\omega\; t} \right)}}}}\end{matrix} & (5)\end{matrix}$So that:

-   A_(0S)=I_(S) ^(Dark)+S·P₀-   A_(0R)=I_(R) ^(Dark)+R·P₀-   A_(1S)=S·ΔP·sin ϕ-   B_(1S)=S·ΔP·cos ϕ-   A_(1R)=R·ΔP·sin ϕ-   B_(1R)=RΔP·cos ϕ

Inspection of equations (4) and (5) shows the output currents have theform of a simple Fourier series consisting of constant DC terms, A_(0S)and A_(0R), plus sine and cosine terms that oscillate with themodulation frequency, ω, with amplitudes A_(1S), A_(1R), B_(1S) andB_(1R).

The dark current terms contribute only to the DC term of the Fourierseries in (4) and (5). The dark current terms are contained within theDC components of equations (4) and (5). Therefore, a simple Fourieranalysis of the modulated output waveform gives the Fourier coefficientsof the sin(ωt) and cos(ωt) terms—which are independent of the darkcurrent.

By measuring the sinusoidally varying component of each output current,the constants, S and R, can be determined without the need to measurethe dark current of each detector diode. These latter terms can beeliminated from the measurement by DC blocking components or byperforming a Fourier analysis of the output currents and discarding allbut the sinusoidal terms.

In conventional spectrometer systems, the dark current would be measuredby blocking off the illumination to the detector diode using a rotatingmechanical chopper that periodically blocks then re-instates the opticalillumination. Using the laser-current modulation described aboveeliminates the need for mechanical components such as rotating chopperswhich simplifies the spectrometer design, reduces cost and improvesreliability by not using any moving parts. Electrical interference fromthe electric motors used to drive mechanical choppers is alsoeliminated.

The method would work as follows with reference to FIG. 19 which is thesame as the method shown in FIG. 4 with the additional dark currentmethod added. The output source electromagnetic radiation would bemodulated using the apparatus in FIG. 16/18 and emitted towards thesample step 190. The affected detected radiation would be received bythe sample and reference detectors 17 and 20 (where used), step 191 andpassed to the processor 18, step 192 for processing. The received outputcan be processed by the processor step 192 to remove the dark current(DC) component A_(0S) and A_(0R) of the received output (as perequations (4), (5) above) and any other unwanted components. The desiredcomponents sin(ωt) and cos(ωt) are obtained and represent the intensitymeasurement without dark current. This processing can be done using anysuitable signal processing know to those in the art. The remaining steps193 and 194 are as previously described.

For example, in one possibility for extracting dark currently step 192,Fourier analysis of the output currents could be performed bymultiplying the outputs by sin(ωt) and cos(ωt) respectively, andintegrating over a period of the oscillation. This can be used where themodulation is a single frequency, e.g. sine wave modulation at a singlefrequency. This procedure provides a form of averaging which isbeneficial in reducing measurement noise.

Alternatively, a Fast Fourier Transform (FFT) algorithm can be appliedto a digitised output waveform and the relevant Fourier componentsextracted. From the Fourier coefficients we therefore obtain:

S·ΔP=√{square root over (A_(1S) ²+B_(1S) ²)} for the sample channel andR·ΔP=√{square root over (A_(1R) ²+B_(1R) ²)} for the reference channel.

Taking the ratio of these Fourier amplitudes eliminates the dependenceon the modulation depth ΔP to give a normalised output, N, given by:

$\begin{matrix}{N = \frac{S}{R}} & (6)\end{matrix}$Values of N are determined at each wavelength of interest and form theoutput data set for the liquid under test.

Other methods for extracting the information could be known and used bythe skilled in the art.

In an alternative analysis process, a reference channel is not used.Rather, the detector output 14 c from affected electromagnetic radiation(from the sample) acquired at an anchor wavelength is used, rather thanthe detector output 15 c from affected electromagnetic radiation fromthe reference in the reference channel. All other detector output 14 cfrom affected electromagnetic radiation received relating to otherwavelengths is normalised/corrected using the detector output ofaffected electromagnetic radiation at the anchor wavelength. The anchorwavelength can be one of the wavelengths already selected, althoughpreferably will be selected to be in the vicinity or within a regionspanning a suitable spectral feature/point in the base liquid spectrum.For example, the anchor wavelength could be in the vicinity of or fallwithin a region spanning a stable region of the base liquid spectrum.Elimination of the reference channel/detector output removes variationbetween the sample and reference channels that can mask sampledifferences, thus removal creates a more sensitive and stable apparatus.The output at the anchor wavelength can be used to normalise, calibrateor otherwise adjust the output for the other wavelengths. The outputfrom the anchor wavelength could be processed in the same manner as theoutput from the reference channel as describe previously in order toverify/analyse the sample. That is, the anchor output can become thereference information.

In one possibility, where water is the base liquid, 1450 nanometres ischosen as the anchor point as there is particular stability in thespectrum of water around this wavelength. This wavelength corresponds tothe maximum optical absorption aqueous solutions due to the presence ofOH bonds. It is a common transmission medium for sample drugs tested.Data acquired at this wavelength shows minimum thermal sensitivity andis therefore provides a highly stable and predictable reference. This isjust one example for water based drug, and is indicative only and shouldnot be considered limiting as to the wavelengths and anchor points thatmight be chosen based on other considerations.

Each of the previous embodiments describe the optional use of areference channel to obtain reference measurements for use in processingdata. In an alternative, the reference channel is not used. Rather, aphotodiode 4 (see FIG. 20) in the laser diode 11 (which is used forpower monitoring and control of the laser diode) can be utilised toobtain reference information. Laser diodes are often fitted withbuilt-in photo-detector diodes 4 that are used to monitor the outputpower of the laser. This is done to stabilise the laser by allowing thelaser driver current to be controlled via a feedback circuitincorporating the integrated photo-diode signal.

This alternative for obtaining reference information can be substitutedin place of the reference channel for any of the embodiments described.The reference measurements obtained using the alternative can beutilised in the same manner as described any previous embodiment.

The output of the laser diode photodetector 4 which detects the outputpower of the source electromagnetic radiation is passed to the processor18 and used instead of reference readings obtained by the referencedetector 20 to normalise and/or correct the output from the detector 17in the sample channel. This output signal from the photodetector 4performs the same function as a reference channel that would otherwisehave been produced more conventionally by using a beam splitterarrangement involving two separate measurement channels. Using thephoto-diode output from the laser as a reference signal therebyeliminates the need for beam-splitting optics and an additionalreference sample and detector.

In an alternative embodiment, the electromagnetic source 11 is abroadband source with multiple filters 13 at different wavelengths thatcan be arranged in between the broadband source and the sample. Theoutput from each filter provides an electromagnetic beam 22 with one ofthe selected wavelengths. The broadband source could be, for example, abroadband filament blackbody source and filters. The source 11 couldalternatively take the form of one or more LEDs with or without filters.Any of the alternative sources could be mounted on a carousel 50 andoperated as described for the first embodiment, or operated inconjunction with an optical device such as described in embodiments twoto four.

Any of the sources could be temperature stabilised with a feedbacksystem, for example by using thermistors and peltier cooling devices aspreviously described.

The detectors could be in the form of one or more InGaAs photodiodes orother light sensors.

A separate photodiode or similar or other detector could be used foreach of the reference and sample channels. Alternatively, a singlephotodiode or similar or other detector could be used for both thesample and reference channels, utilising optical devices to merge theaffected radiation beams of both channels, or otherwise direct them tothe detector.

Random errors in measurements can be reduced by averaging detectorreadings over many measurements (e.g. 500). Dark measurements (sourceoff) can be used to correct measured data.

For dark current readings, a chopper wheel can optionally be used thatblacks out/blocks the electromagnetic radiation 22 incident on thesample 16 and the reference 20. The chopper could form part of theoptical device 13. For each electromagnetic reading, the detector 17/20also takes a “dark” reading when the chopper blocks the electromagneticradiation 22. Having a chopper wheel and dark reading is not essentialfor the invention and is described here as one possible option.

Over the band 1300 nm to 2000 nm, it is also possible to use a singletype of photo-diode detector based on indium gallium arsenide (InGaAs)technology which further simplifies the detector system.

The present invention preferably uses wavelengths in the analysis regionof 1300 nm to 2000 nm or variations thereof. This region has previouslybeen ignored for drug analysis due to the perceived disadvantage ofbroad spectral peaks and troughs that appear in the absorbance spectrum.Infra-red (IR) spectroscopy previously has exploited the numerousnarrow-band spectral absorption characteristics that exist forwavelengths longer than 2000 nm. This so-called ‘finger-print’ regionexhibits spectral lines that are characteristic of certain chemicalbonds present in the material under test and offers a highly sensitivetechnique to identifying the material. The present inventors havedetermined that the 1300 nm-2000 nm analysis range (or portions thereof)provides an advantage for drug verification or identification or otheranalysis. Further, the inventors have established that the spectrallocation of salient spectral features in this analysis region is lessaffected by temperature variations. The numerous narrow spectral bandsthat appear in the region above 2000 nm exhibit large temperaturesensitivity. If this region above 2000 nm is used for verification oridentification, the analysis apparatus requires very precise wavelengthresolution. This resolution can only be achieved using high-costsophisticated spectrometers

More particularly, this type of IR spectroscopic measurement (above 2000nm) requires very fine wavelength resolution (typically a fewnanometres) maintained over a wide spectral band in order to resolve thenumerous individual spectral features. The fine wavelength resolution isespecially required to account for any shift in the narrow spectrallines with respect to temperature variations.

The measurement of such highly resolved spectral lines requires the useof a spectrometer fitted with a sophisticated monochromator based eitheron a mechanically rotated diffraction grating and single detector, or afixed grating with a linear array of detector elements. Both options arefound in existing spectrometers and both are expensive to implement.

As a cost-effective alternative, aimed for example at water-basedintravenous drug verification/identification or other analysis, it hasbeen determined by the present inventors that it is advantageous to makemeasurements within the shorter wavelength region between 1300 nm and2000 nm. Whilst the spectral characteristics/features in this wavelengthregion are much fewer in number and much broader spectrally (differinglittle from those of water), the inventors have found that there remainsufficient spectral differences between drugs (or other liquid basedsamples) to facilitate verification/identification. The have also found,that, in the 1300 nm to 2000 nm region, the wavelengths at which thepeaks and troughs (and other spectral characteristics) of each drug's IRtransmission spectrum occur remain highly stable with respect totemperature for all water-based drugs (or other samples).

Importantly, due to the absence of temperature-sensitive narrow spectralabsorption features, they have established there is no requirement forhighly resolved spectral lines to be measured thereby eliminating theneed for an expensive monochromator. A small number of measurements (5or 6 typically) made at discrete wavelengths over the range 1300 nm to2000 nm is sufficient to characterise each drug (or other sample).Typically, each measurement is made over a bandwidth of 12 nm (asdetermined by a band-pass filter, illuminated by a broad-band source,for example) or over a few nanometres for laser-based illumination.

What is claimed is:
 1. An analyser for identifying or verifying a liquiddrug for delivery to a patient to reduce risk of adverse drug events,the liquid drug comprising a drug in a base liquid, the liquid drughaving a liquid drug spectrum and the base liquid having a base liquidspectrum comprising at least one spectral characteristic feature betweensubstantially 1300 nm and 2000 nm, the analyser comprising: anelectromagnetic radiation source for emitting electromagnetic radiationat the liquid drug, the electromagnetic radiation comprising a pluralityof different wavelengths between substantially 1300 nm and 2000 nm,wherein at least one of the wavelengths is at or in the vicinity of orwithin a region spanning a wavelength of a spectral characteristicfeature of the base liquid spectrum, a liquid drug detector that detectsaffected electromagnetic radiation resulting from the emittedelectromagnetic radiation affected by the liquid drug and that providesoutput representing spectral information of the liquid drug spectrum atthe wavelengths, and a processor configured to identify or verify theliquid drug from the detector output by: querying a database ofreference liquid drugs and corresponding spectral information of thereference liquid drugs at the wavelengths, each reference liquid drugcomprising a reference drug in a base liquid, each reference liquid drughaving a reference liquid drug spectrum and the base liquid having abase liquid spectrum comprising the at least one spectral characteristicfeature between substantially 1300 nm and 2000 nm, there beingsufficient spectral differences between the reference liquid drugspectrums at the least one spectral characteristic feature of the baseliquid spectrum to provide discrimination between reference drugs, andidentifying or verifying the liquid drug using: a) the detector outputrepresenting the spectral information of the liquid drug, and b) thespectral information of the reference liquid drugs, wherein thediscrimination between the reference drugs assists with the identifyingor verifying the liquid drug.
 2. An analyser according to claim 1wherein the electromagnetic radiation comprises a plurality ofelectromagnetic radiation beams, each beam having a differentwavelength.
 3. An analyser according to claim 1 wherein the wavelengthsspan or capture a plurality of at least some of the spectralcharacteristic features in the liquid spectrum between 1300 nm and 2000nm.
 4. An analyser according to claim 1 wherein the liquid spectrumcomprises two or more spectral characteristic features, and wherein:each spectral characteristic feature falls in or spans a region of theliquid spectrum, and each wavelength falls within one of the regions. 5.An analyser according to claim 1 wherein the spectral characteristicfeatures comprise peaks, troughs, inflections, stable points or regions,plateaus, knees and/or slopes of the liquid spectrum.
 6. An analyseraccording to claim 1 wherein the source is a plurality of lasers in asingle package, each laser configured to emit an electromagneticradiation beam at a fixed or tuneable wavelength.
 7. An analyseraccording to claim 1 wherein the detector and/or source are temperaturecompensated to provide temperature stability, using thermistors andpeltier devices in a closed loop system.
 8. An analyser according toclaim 1 wherein the processor, as part of identifying or verifying theliquid drug from the output from the detector: turns off the source andmeasures the output of the detector, resulting in a dark currentcomponent, and removes the dark current component from the outputrepresenting the detected affected electromagnetic radiation.
 9. Ananalyser according to claim 1 wherein the source is further operated toemit electromagnetic radiation at the detector unaffected by the liquiddrug, and the processor, as part of identifying or verifying the liquiddrug from the output from the detector, measures output of the detectorresulting from the emitted electromagnetic radiation unaffected by theliquid drug.
 10. A method for identifying or verifying a liquid drug fordelivery to a patient to reduce risk of adverse drug events, the liquiddrug comprising a drug in a base liquid, the liquid drug having a liquiddrug spectrum and the base liquid having a base liquid spectrumcomprising at least one spectral characteristic feature betweensubstantially 1300 nm and 2000 nm, the method comprising: emittingelectromagnetic radiation at the liquid drug, the electromagneticradiation comprising a plurality of different wavelengths betweensubstantially 1300 nm and 2000 nm, wherein at least one of thewavelengths is at or in the vicinity of or within a region spanning awavelength of a spectral characteristic feature of the base liquidspectrum, detecting affected electromagnetic radiation resulting fromthe emitted electromagnetic radiation affected by the liquid drug andproviding output representing spectral information of the liquid drugspectrum at the wavelengths, querying a database of reference liquiddrugs and corresponding spectral information of the reference liquiddrugs at the wavelengths, each reference liquid drug comprising areference drug in a base liquid, each reference liquid drug having areference liquid drug spectrum and the base liquid having a base liquidspectrum comprising the at least one spectral characteristic featurebetween substantially 1300nm and 2000nm, there being sufficient spectraldifferences between the reference liquid drug spectrums at the least onespectral characteristic feature of the base liquid spectrum to providediscrimination between reference drugs, and identifying or verifying theliquid drug using: a) the output representing the spectral informationof the liquid drug, and b) the spectral information of the referenceliquid drugs, wherein the discrimination between the reference drugsassists with the identifying or verifying the liquid drug.
 11. A methodaccording to claim 10 wherein the electromagnetic radiation comprises aplurality of electromagnetic radiation beams, each beam having adifferent wavelength.
 12. A method according to claim 10 wherein thewavelengths span or capture a plurality of at least some of the spectralcharacteristic features in the liquid spectrum between 1300 nm and 2000nm.
 13. A method according to claim 10 wherein the liquid spectrumcomprises two or more spectral characteristic features, and wherein:each spectral characteristic feature falls in or spans a region of theliquid spectrum, and each wavelength falls within one of the regions.14. A method according to claim 10 wherein the spectral characteristicfeatures comprise peaks, troughs, inflections, stable points or regions,plateaus, knees and/or slopes of the liquid spectrum.
 15. A methodaccording to claim 10 wherein the electromagnetic radiation is generatedusing a source comprising a plurality of lasers, each laser configuredto emit an electromagnetic radiation beam at a fixed or tuneablewavelength.
 16. A method according to claim 10 wherein the detectorand/or source are temperature compensated to provide temperaturestability, using thermistors and peltier devices in a closed loopsystem.
 17. A method according to claim 10 further comprising: turningoff the source and measuring the output, resulting in a dark currentcomponent, and removing the dark current component from the outputrepresenting the detected affected modulated electromagnetic radiation.18. A method according to claim 10, wherein the output is provided by adetector, the method further comprising emitting electromagneticradiation at the detector so it is unaffected by the liquid drug, andmeasuring the output of the detector resulting from the emittedelectromagnetic radiation unaffected by the liquid drug.